US8386044B2 - Complex connector in component footprint of implantable medical device - Google Patents
Complex connector in component footprint of implantable medical device Download PDFInfo
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- US8386044B2 US8386044B2 US11/290,282 US29028205A US8386044B2 US 8386044 B2 US8386044 B2 US 8386044B2 US 29028205 A US29028205 A US 29028205A US 8386044 B2 US8386044 B2 US 8386044B2
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/375—Constructional arrangements, e.g. casings
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01G—CAPACITORS; CAPACITORS, RECTIFIERS, DETECTORS, SWITCHING DEVICES OR LIGHT-SENSITIVE DEVICES, OF THE ELECTROLYTIC TYPE
- H01G9/00—Electrolytic capacitors, rectifiers, detectors, switching devices, light-sensitive or temperature-sensitive devices; Processes of their manufacture
- H01G9/004—Details
- H01G9/008—Terminals
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01G—CAPACITORS; CAPACITORS, RECTIFIERS, DETECTORS, SWITCHING DEVICES OR LIGHT-SENSITIVE DEVICES, OF THE ELECTROLYTIC TYPE
- H01G9/00—Electrolytic capacitors, rectifiers, detectors, switching devices, light-sensitive or temperature-sensitive devices; Processes of their manufacture
- H01G9/004—Details
- H01G9/08—Housing; Encapsulation
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/375—Constructional arrangements, e.g. casings
- A61N1/37512—Pacemakers
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01R—ELECTRICALLY-CONDUCTIVE CONNECTIONS; STRUCTURAL ASSOCIATIONS OF A PLURALITY OF MUTUALLY-INSULATED ELECTRICAL CONNECTING ELEMENTS; COUPLING DEVICES; CURRENT COLLECTORS
- H01R2201/00—Connectors or connections adapted for particular applications
- H01R2201/12—Connectors or connections adapted for particular applications for medicine and surgery
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- Engineering & Computer Science (AREA)
- Power Engineering (AREA)
- Health & Medical Sciences (AREA)
- Microelectronics & Electronic Packaging (AREA)
- Public Health (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Radiology & Medical Imaging (AREA)
- Veterinary Medicine (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Biomedical Technology (AREA)
- Cardiology (AREA)
- Heart & Thoracic Surgery (AREA)
- Electrotherapy Devices (AREA)
- Prostheses (AREA)
Abstract
A complex connector and component within an implantable medical device in which the complex connector is positioned within the spacing footprint of the component to optimize packaging within the device.
Description
This application is a divisional of prior application Ser. No. 10/266,651, filed Oct. 27, 2002, now abandoned entitled “Complex Connector in Component Footprint of Implantable Medical Device.”
An energy storage and delivery component for an implantable medical device having an imbedded electrical connector.
Within the field of implantable medical devices, there exists a constant need to reduce the space and volume requirements of each device while increasing the capabilities of the same device. Considerable improvements in capability have occurred with developments in the power management and electronics assemblies in such devices. Further developments included shaping of components within the devices to permit improved outer shaping of the devices.
One class of internal components of such devices is an energy storing and delivery component, such as a battery or capacitor. Again, improvements in the design of this class of component have resulted in reduced space and volume requirements while maintaining capabilities. Yet this area has overlooked the use of certain improvements to achieve more efficient manufacturing and packaging attributes.
Applicants have identified methods and structure to permit the use of compound side shapes on the housings of energy storage and delivery devices which enable flush mounting of improved electrical connectors. In one embodiment, a method is taught for assembling an electrical connector with an energy storage and delivery component for use within an implanted medical device. The method comprises the steps of providing an energy storage and delivery component that is shaped to connect with an embedded complex electrical connector. The embedded electrical connector is sized to fit within a space formed within a notched zone defined by linear extensions of two perimeter surfaces of the energy storage and delivery component. A metallic insert is stamped out of raw sheet stock and then metal plated with a conductive plating material. A resinous connector portion is injection or cast molded with the metallic insert forming an integrated electrical connector for use in the implantable medical device, with said forming comprising creation of channel shaped wire-ways each sized to receive an un-insulated electrical wire connector from the energy storage and delivery device component. The electrical connector is then positioned into the notched zone on the energy storage and delivery device, and either an insulated or an un-insulated electrical wire then positioned into a wire-way.
In another embodiment, an implantable medical device having at least one capacitor for storing and delivering electrical energy on demand is provided. The at least one capacitor has a related connector for electrically connecting the capacitor with at least one other component within the device. The capacitor is shaped to connect with an embedded electrical connector which is sized to fit within a space formed within a zone defined by linear extensions of two perimeter surfaces of the capacitor.
In another embodiment, an implantable cardiac defibrillation device is provided which includes at least one flat capacitor for storing and delivering electrical energy on demand. The capacitor has at least a 30 Joule capacity; and the device has a volume of less than about 36 cubic centimeters and a thickness of less than about 15 millimeters, although other configurations are also disclosed.
The capacitor also has a related connector for electrically connecting the capacitor with at least one other component within the device. The capacitor is shaped to connect with the embedded electrical connector that is sized to fit within a space formed within a zone defined by linear extensions of two perimeter surfaces of the capacitor.
In yet another embodiment, an implantable medical device electrical connector is provided for connecting at least one energy storage and delivery component to at least one other component within the device. The connector comprises a stamped metallic portion for providing electrical connection between electrical connectors of an energy storage and delivery component and another component within the implantable medical device. The connector also has an injection molded connector portion formed in contact with the stamped metallic portion to provide a plurality of wire pathways shaped to receive electrical connectors from at least one energy storage and delivery component. The wire pathways also guide the energy storage and delivery component electrical connectors into selective electrical contact with conductive portions of the stamped metallic portion.
Various techniques have been attempted and utilized to reduce the volume and improve the shape of implantable medical devices. In particular, those devices requiring discharge of high energy shocks such as implantable cardioverters or defibrillators require considerable efficiencies in order to maintain the overall device weight and size dimensions within commercial and medical tolerances. One area which has been overlooked as a source of improved packaging is that of reducing the margin area around sub-assemblies or components within such implantable medical devices. Rather it is quite common to have sizable percentages of dead space or non-useful volume within component housings and around the components themselves. Applicants have recognized this packaging problem and have identified several ways of reducing this lost volume while simultaneously decreasing the cost of assembling devices which achieve these benefits. Applicants are able to efficiently design and assemble energy storage and delivery components which are shaped to receive an embedded electrical connector placed within a zone defined by linear extensions of two perimeter or housing side surfaces of the energy storage and delivery device.
Examples in the prior art demonstrate part of the need for these innovations. FIG. 1 is a plan view of an implantable cardioverter 10 which includes capacitors 13, a battery 16, and electronics assemblies 19, 20. As shown, for example at arrows 22, a considerable percentage of the volume within the device housing 24 is not used, or is partially used for electrical connection structure 28 protruding from the outer perimeter footprint of components. FIG. 2 is a plan view of an implantable cardiac defibrillator 30. Again, as shown by protruding electrical connector 33, the result of such protrusions or extensions beyond the perimeter footprint of components creates considerable unusable space shown by arrows 35. This is partly due to the inability of device manufacturers to make components in an integrated manner and with various shapes and sizes of components to accommodate and fit closely around protruding electrical connections.
It is recognized that known energy storing and delivery components for implantable medical devices, particularly capacitors, have a limited array of shapes. These include cylindrical, flat, semi-circle or rounded semi-rectangle. Other shapes are shown for example in U.S. Pat. No. 6,426,864, which includes that shape as depicted in capacitor 40 in FIG. 3 . FIG. 4 discloses a capacitor 45 internal configuration as shown in U.S. Pat. No. 6,191,931. That figure also shows a feed-through wire 47 attached to anode tabs and designed for extending through and beyond a capacitor outer housing using a rigid plastic-encased sleeve 49. FIGS. 5 and 6 illustrate an energy storage and delivery component 50, which in this example is a capacitor, with protruding electrical connector 55. FIG. 6 shows the effect of a protruding electrical connector structure requiring inefficient use of substantial side volume V1 between the component 50 and the device housing wall 58.
It is clear that there are undesirable packaging results of electrical connector structure which protrude beyond a component periphery or normal footprint within an implantable medical device. However, there are further negative effects (including, for example, electrical shorting, reliability, and liability exposure) which occur when attempts are made to use electrical connections that are loosely configured wires or not properly insulated or protected wires. One example of this is shown in FIG. 7 in which capacitors 64 are connected via loose wire connections 67 to an electrical assembly within an implantable cardiac defibrillator (ICD) 70. Electrical connections of this type are often hand manufactured by one or more technicians, rather than by an automated process operator (i.e., machine). This adds cost and may inject loss of reliability into the manufacturing process. FIG. 8 shows an external connection for a pulse generator 70, having a headerless design, aligned with the terminal end portion of a stimulating lead 72. The lead 72 has a connector 74 attached to the terminal end, wherein the connector 74 is adapted for connection with the feed-through assembly 76 of the pulse generator 70. An elastomeric boot 78 is sealingly engaged to the lead 72, whereby the boot may be slid over the lead to the terminal end of the lead, to thereby cover the connector 74. The invention of FIG. 8 relates to a connection of a stimulating lead for stimulating tissue to the external portion of a stimulation device. The figure not does relate to the connections or packaging between components within an implantable medical device.
What is needed to overcome these packaging concerns is an embedded connector block for use with an implantable medical device component, including, for example, an energy storage and delivery component, which integrates into a component footprint rather than adding to the footprint. FIGS. 9-32 show embodiments of devices, components, assemblies, sub-assemblies and connectors which achieve this goal. FIG. 9 is a plan view of a cover or housing 85 for a representative component, which in this embodiment is a capacitor. The housing has a plurality of outer peripheral surfaces 89, 91, 93, 96, 99, 102 and 105. As compared with known capacitor covers/housings, housing 85 has at least one additional surface in plan view. Actually, as compared to either a rectangular or semi-circular housing (or other energy storage and delivery device sized for placement therein) the housing shown in FIG. 9 discloses a plurality of notched zones 110 formed within an area defined by linear extensions (shown by dashed lines E1 and E2) of perimeter surfaces of the housing 85 (or energy storage and delivery component). An even smaller zone may be formed using linear extension E3, if desired. Each notched zone 110 is sized to receive a complex electrical connector (shown and described later herein) which is designed for that zone, and said connector electrically connects at least one energy storage and delivery component to other components or assemblies within an implantable medical device. Other surfaces may be shaped to receive other complex connectors as well within similarly created zones which also remain within the conventional shape or footprint of the component. The creation of these zones virtually eliminates the protrusions and other problems shown in the prior art devices, including all of those shown in FIGS. 1-8 , and enables improved packaging through closer flush-mounting of components and efficient use of such novel complex connectors as shown and described herein.
Additional features are added to connector 335. For example, FIG. 17 shows the stamped metallic portion having a breakaway groove 501 in a lower surface 513 between the common lead frame and the stamping legs. That portion of upper surface 515 that is opposite breakaway groove is flat, i.e. without a groove, to assist in the clean break of the material. Also, breakaway groove 501 comprises wall portions 518 shaped to allow reliable separation of the common lead frame from the stamping legs to eliminate any post-molding trim of the injection molded connector. Also, the wall portions 518 are arranged to direct the separation of the common lead frame from the stamping legs at a location inside an outer periphery of the connector to provide a flash free shutoff at the groove locations.
In addition to the considerable manufacturing efficiencies and cost savings which result from use of this invention, improved implantable medical devices are enabled. For example, in one embodiment there is provided at least one capacitor (or other energy storage and delivery component) for storing and delivering electrical energy on demand that has at least a 30 Joule capacity, a volume of less than about 36.5 cubic centimeters and a thickness of less than about 14 millimeters. In another embodiment, the invention includes at least one capacitor for storing and delivering electrical energy on demand which has at least a 30 Joule capacity, a volume of less than about 33 cubic centimeters and a thickness of less than about 13.5 millimeters. A further embodiment has at least one flat capacitor for storing and delivering electrical energy on demand, and the capacitor has at least a 30 Joule capacity. In this embodiment the device has a volume of less than about 36 cubic centimeters and a thickness of less than about 15 millimeters. In each of these embodiments, the capacitor has a related connector for electrically connecting the capacitor with at least one other component within the device. The capacitors are shaped to connect with an embedded electrical connector that is sized to fit within a space formed within a zone defined by linear extensions of two perimeter surfaces of the capacitor.
Another way of expressing this invention is an implantable medical device which has at least one internal component for energy storage and delivery of a defibrillation shock to a user. The internal component has a first energy storage and delivery capacity and a first volume, and the internal component is shaped to connect with an embedded electrical connector that is sized to fit within a space formed within a zone defined by linear extensions of two perimeter surfaces of the internal component. The first storage and delivery capacity is at least as great as any other known energy storage and delivery internal component less than about 36 Joules, and the first volume is less than the volume of any other identified energy storage and delivery internal component having the identical energy storage and delivery capacity.
Thus, embodiments of a connector block in a component footprint of an implantable medical device are disclosed. One skilled in the art will appreciate that the present invention can be practiced with embodiments other than those disclosed. For example, the connector block may be formed in an assembly of a plurality of sub-connector blocks. The disclosed embodiment are presented for purposes of illustration and not limitation, and the present invention is limited only by the claims that follow.
Claims (9)
1. An implantable cardiac medical device comprising:
at least one flat capacitor for storing and delivering electrical energy on demand, the capacitor having at least a 30 Joule capacity; the device having a volume of less than about 36 cubic centimeters and a thickness of less than about 15 millimeters; and
said capacitor has a related connector for electrically connecting the capacitor with at least one other component within the device;
an embedded complex electrical connector,
wherein the capacitor is shaped to connect with the embedded complex electrical connector that is sized to fit within a space formed within a notched zone defined by linear extensions of two perimeter surfaces of a housing of the capacitor.
2. The device of claim 1 in which the embedded electrical connector comprises a stamped metal piece and an injection molded thermoplastic or cast thermoset piece forming a connector with at least four wire-ways each shaped to receive and protect a bare metal wire connector from an associated capacitor.
3. The device of claim 1 in which the embedded electrical connector is sized to fit within the space formed within the zone so that a wall to wall component may be positioned adjacent to the capacitor without the connector creating any margin area between the capacitor and the battery.
4. The device of claim 2 in which the connector wire ways are arranged so that two wire ways connect to a common electrical connector on the stamped metal piece and each of the two additional wires are split among the positive and negative voltage electrical connectors on the stamped metal piece, and wherein each wire way is bounded by finger elements of the thermoplastic or thermoset material raised above the height of the wire in each wire way.
5. An implantable cardiac defibrillator medical device comprising:
at least one internal component for energy storage and delivery of a defibrillation shock to a user, said internal component having a housing of a first volume and providing a first energy storage and delivery capacity; and
an embedded electrical connector;
said internal component is shaped to connect with the embedded electrical connector, the embedded electrical connector being sized to fit within a space formed within a notched zone defined by linear extensions of two perimeter surfaces of the internal component; and
said first storage and delivery capacity being less than about 40 Joules.
6. The device of claim 5 in which the at least one internal component is a flat capacitor.
7. The device of claim 5 in which the embedded electrical connector comprises a stamped metal piece and an injection molded thermoplastic or cast thermoset piece forming a connector with at least one wire-way shaped to receive and protect a bare metal wire connector from an associated capacitor.
8. The device of claim 5 in which the embedded electrical connector is sized to fit within the space formed within the zone so that a wall to wall component may be positioned adjacent to the capacitor without the connector creating any margin area between the capacitor and the battery.
9. The device of claim 5 in which the at least one capacitor for storing and delivering electrical energy on demand has at least a 30 Joule capacity, and a volume of less than about 35 cubic centimeters.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/290,282 US8386044B2 (en) | 2002-10-07 | 2005-11-30 | Complex connector in component footprint of implantable medical device |
US13/777,625 US8825160B2 (en) | 2002-10-07 | 2013-02-26 | Complex connector in component footprint of implantable medical device |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/266,651 US8249710B2 (en) | 2002-10-07 | 2002-10-07 | Complex connector in component footprint of implantable medical device |
US11/290,282 US8386044B2 (en) | 2002-10-07 | 2005-11-30 | Complex connector in component footprint of implantable medical device |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US10/266,651 Division US8249710B2 (en) | 2002-10-07 | 2002-10-07 | Complex connector in component footprint of implantable medical device |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US13/777,625 Continuation US8825160B2 (en) | 2002-10-07 | 2013-02-26 | Complex connector in component footprint of implantable medical device |
Publications (2)
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US20060172611A1 US20060172611A1 (en) | 2006-08-03 |
US8386044B2 true US8386044B2 (en) | 2013-02-26 |
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US10/266,651 Active 2024-10-02 US8249710B2 (en) | 2002-10-07 | 2002-10-07 | Complex connector in component footprint of implantable medical device |
US11/290,282 Active 2026-03-19 US8386044B2 (en) | 2002-10-07 | 2005-11-30 | Complex connector in component footprint of implantable medical device |
US13/777,625 Expired - Fee Related US8825160B2 (en) | 2002-10-07 | 2013-02-26 | Complex connector in component footprint of implantable medical device |
Family Applications Before (1)
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US10/266,651 Active 2024-10-02 US8249710B2 (en) | 2002-10-07 | 2002-10-07 | Complex connector in component footprint of implantable medical device |
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US13/777,625 Expired - Fee Related US8825160B2 (en) | 2002-10-07 | 2013-02-26 | Complex connector in component footprint of implantable medical device |
Country Status (5)
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US (3) | US8249710B2 (en) |
EP (1) | EP1558337B1 (en) |
JP (1) | JP2006501959A (en) |
CA (1) | CA2501654A1 (en) |
WO (1) | WO2004033035A2 (en) |
Cited By (1)
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US8825160B2 (en) | 2002-10-07 | 2014-09-02 | Medtronic, Inc. | Complex connector in component footprint of implantable medical device |
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Also Published As
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WO2004033035A3 (en) | 2004-09-16 |
US8249710B2 (en) | 2012-08-21 |
US20130238071A1 (en) | 2013-09-12 |
JP2006501959A (en) | 2006-01-19 |
US20060172611A1 (en) | 2006-08-03 |
EP1558337A2 (en) | 2005-08-03 |
US8825160B2 (en) | 2014-09-02 |
CA2501654A1 (en) | 2004-04-22 |
US20040068302A1 (en) | 2004-04-08 |
WO2004033035A2 (en) | 2004-04-22 |
EP1558337B1 (en) | 2014-09-10 |
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